WO1999053832A1 - Imaging system with automatic gain control for reflectance and fluorescence endoscopy - Google Patents
Imaging system with automatic gain control for reflectance and fluorescence endoscopy Download PDFInfo
- Publication number
- WO1999053832A1 WO1999053832A1 PCT/US1999/007789 US9907789W WO9953832A1 WO 1999053832 A1 WO1999053832 A1 WO 1999053832A1 US 9907789 W US9907789 W US 9907789W WO 9953832 A1 WO9953832 A1 WO 9953832A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- light
- fluorescence
- rem
- light source
- image
- Prior art date
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/04—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor combined with photographic or television appliances
- A61B1/043—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor combined with photographic or television appliances for fluorescence imaging
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/00002—Operational features of endoscopes
- A61B1/00004—Operational features of endoscopes characterised by electronic signal processing
- A61B1/00009—Operational features of endoscopes characterised by electronic signal processing of image signals during a use of endoscope
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
- A61B1/04—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor combined with photographic or television appliances
- A61B1/045—Control thereof
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0071—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by measuring fluorescence emission
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
- A61B5/0084—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for introduction into the body, e.g. by catheters
Definitions
- the present invention relates to imaging systems for medical endoscopy, in general and to endoscopic imaging systems for fluorescence and reflectance endoscopy, in particular.
- white light optical fiber endoscopy One common diagnostic technique used by physicians to detect diseases within a body cavity of a patient is white light optical fiber endoscopy.
- white light is directed into the body cavity via a non-coherent fiber-optic illumination guide of an endoscope.
- the light illuminates the tissue under examination and the reflected illumination light is gathered and transmitted through a coherent fiber-optic imaging guide of the endoscope.
- the image formed by the reflected white light at the end of the imaging guide may be viewed directly through the endoscope eyepiece or may be imaged by a color video camera connected to the eyepiece. Images transduced by the camera are then typically transmitted to an image processing storage device and to a video monitor where they can be viewed by the physician.
- the diflFerences in the autofiuorescence (also referred to as native fluorescence) spectrum of normal and abnormal tissue can be exploited.
- fluorescence optical fiber endoscopy a fluorescence excitation light is delivered into the body cavity via the illumination guide of the endoscope. The wavelengths of this light are matched to the absorption spectrum of the naturally -2-
- the fluorescence excitation light causes the tissue in the body cavity to fluoresce with a green and red emission spectrum and the resulting light is collected and transmitted through the optical fiber imaging guide of the endoscope.
- the resulting image is transduced by a camera that filters out any reflected blue light and divides the autofluorescence into two broad (green and red) spectral bands.
- the image formed by the light in each spectral band is projected onto a separate intensified CCD (ICCD) transducer and the resulting signal is fed into a control center for processing, storage and, finally, for display on a video monitor.
- ICCD intensified CCD
- the current LIFE-Lung System has a number of limitations, however.
- the current embodiment of the system requires the physician to manually adjust the gain of the system (i.e., to increase and decrease the camera's sensitivity to the tissue autofluorescence). This is a cumbersome task for the physician to perform, when he/she is simultaneously trying to maneuver the endoscope in the patient.
- automatic gain control circuits for video systems are widely available, they do not provide adequate gain control for the complex scene conditions encountered in imaging autofluorescence with ICCDs. If, for example, the average brightness of an image is increased to an acceptable level, there may be bright spots that can damage the ICCDs.
- a second limitation of the current LIFE-Lung System becomes evident when a physician wishes to switch between white light (reflectance) and fluorescence imaging modes.
- the physician must switch light sources and cameras manually (i.e., from a white light illumination source to a fluorescence excitation light source and from an RGB color video camera to the fluorescence camera).
- One technique for addressing this time consuming process is to have all light sources and cameras connected to the endoscope simultaneously and to utilize a mode switching mechanism to switch from one imaging mode to the other.
- some precaution must be taken in the implementation of a switching mechanism since the ICCDs can be damaged if they are subjected to the bright, reflected illumination light.
- a third limitation of the current LIFE-Lung System is that a physician viewing the image displayed by the system has no way of objectively quantifying the extent of abnormality exhibited by the tissue under examination.
- the effective use of the system is dependent on such subjective factors as the physician's ability to distinguish color and his/her ability to interpret this color information in the context of other image features.
- a means to objectively quantify the difference in the autofluorescence spectra of normal and abnormal tissue, or even an additional means to subjectively differentiate these tissues based on their difference in autofluorescence spectra could improve the clinical usability of this system. This can be accomplished using computational techniques using the spectral information of the emitted fluorescence and displaying the results on the monitor together with the images.
- an automatic gain control circuit that will optimally adjust the brightness of autofluorescence images and that will maintain a defined relationship between the two channels of the imaging system;
- the present invention is an imaging system for white light and fluorescence endoscopy that includes a particular automatic gain control (AGC) circuit in the fluorescence imaging mode.
- the AGC circuit adjusts the gain of the imaging system by adjusting the gain of two high sensitivity imaging devices such as image intensified CCD (ICCDs) transducers in a fluorescence camera head and by adjusting the light intensity of the excitation light source.
- the video signals from a pair channels (the "green” and “red” channel) of a fluorescence camera are supplied to a set of counters.
- the counters consisting of counters connected to a clocking oscillator, measure the length of time each video signal has a magnitude that exceeds a reference threshold that is individually set for each counter.
- the outputs of the counters can be made to indicate the distribution of video signal amplitudes in one or more video fields.
- a decision tree algorithm determines if the gain of the imaging system or the light source intensity should be increased or decreased.
- a gain control equation determines the appropriate value of light source intensity change and maps the resulting imaging system gain increase or decrease to an individual gain change for each ICCD transducer such that the relative gain between the two channels remains the same.
- the present invention also includes a mode switching mechanism that allows for convenient switching between white light and fluorescence endoscopy imaging modes.
- mode switching implies that white light and fluorescence light sources and cameras are connected to the endoscope simultaneously and that the appropriate combination of camera and light source are activated when switching modes.
- This requires a two-part mode switching mechanism: one switching the cameras and one switching the light sources.
- the camera mode switching mechanism consists of a light directing mechanism such as a mirror that is movable between a first position, where the image from the endoscope is reflected towards an RGB video camera head, and a second position, where the image from the endoscope is allowed to pass to the fluorescence camera head.
- the light source mode switching mechanism consists of a filter driver that positions blue, fluorescence excitation filters or white light filters in an illumination light path that extends between the light source and an endoscope.
- the present invention also provides a means of objectively quantifying the spectral differences between normal and abnormal tissue by using the relative brightness of autofluorescence in the spectral bands being imaged (green and red). A portion of the autofluorescence image is analyzed and the numerical value defined by a particular mathematical function such as the ratio of the image brightnesses of the two wavebands is displayed for the physician.
- FIGURE 1 is a block diagram of an imaging system for white light and fluorescence endoscopy according to the present invention
- FIGURE 2 is a block diagram of a light source used in the imaging system for white light and fluorescence endoscopy shown in FIGURE 1;
- FIGURE 3 is a block diagram of an automatic gain control circuit in accordance with a first aspect of the present invention
- FIGURE 4 is a block diagram of a number of comparators and time-over threshold counters that are included in the automatic gain control circuit shown in FIGURE 3;
- FIGURE 5 is a flowchart illustrating the steps performed by the present invention to change the gain of the imaging system shown in Figure 3 or the intensity of light produced by the light source shown in Figure 2;
- FIGURE 6 is a block diagram of an imaging mode switching mechanism located in the combination camera head in accordance with another aspect of the present invention.
- FIGURE 7 is a pictorial illustration of an autofluorescence image that includes a quantitative indication of the relative intensities of the autofluorescence light present in two spectral bands in accordance with another aspect of the present invention.
- the present invention is an imaging system for white light and fluorescence endoscopy that includes an automatic gain control (AGC) circuit in the fluorescence imaging mode.
- the AGC circuit controls the image brightness in two ways, a) by adjusting the gain of the two image-intensified CCDs (ICCDs) transducers in a fluorescence camera head, and b) by adjusting the intensity of an excitation light source.
- AGC automatic gain control
- the input to the AGC circuit are the two video signals (a green and red channel) produced by the fluorescence camera.
- the video signals are supplied to a set of counters that determine a total period of time during which the video signal has a magnitude that exceeds reference threshold (set individually for each counter).
- the outputs of the counters are indicative of the distribution of video signal amplitudes in one or more video fields.
- a decision tree algorithm determines if the gain of the imaging system or light source intensity should be increased or decreased.
- a gain control equation determines the appropriate value of light source intensity change and maps the gain increase or decrease to an individual gain change for each ICCD such that the relative gain between the two channels remains the same.
- FIGURE 1 is a block diagram of an imaging system 10 for white light and fluorescence endoscopy according to the present invention.
- a control center 20 that includes a central processing unit 22 that is programmed to control the operation of the system including a combination light source 36 and a combination camera head 42.
- An internal random access memory (RAM), a hard disk drive and read-only memory (ROM) 24 stores a computer software program that controls the operation of the central processing unit 22.
- the memory also allows the storage of data such as acquired images, parameters and log files.
- a number of controls 26 on a front panel of the control center 20, allow an operator to adjust the operation of the imaging system.
- the control center 20 also includes an imaging board 28 that receives analog video signals that originate from a number of sources including a fluorescence camera head 44 and an RGB camera head 46 that are enclosed within the combination camera head 42.
- a video switch that is part of a digital and video I O 32, receives and selects the fluorescence or RGB video signals to be supplied as an input to the -7-
- the imaging board 28 digitizes the selected video signal, then processes and converts the digitized signals to appropriate signals to be displayed on a video monitor 54.
- the combination light source 36 provides the white light and fluorescence excitation light.
- the control center 20 is interfaced with the light source 36 through status and control lines 102, 106, and 108.
- Broadband white illumination light or fluorescence excitation light (typically at 437nm ⁇ lOnm) is supplied from the combination light source 36 to an illumination guide 38 of a fiber-optic endoscope 40.
- Light from the illumination guide 38 illuminates an internal body cavity of a patient. Reflected white light or autofluorescence light from the tissue under examination is transmitted by an imaging guide of the fiber-optic endoscope 40 and is projected onto the combination camera head 42.
- the combination camera head 42 also includes a mode switch mechanism 67 that directs the light received from the endoscope 40 to either the RGB video camera head 46 or the fluorescence camera head 44.
- the fluorescence camera head 44 With the fluorescence imaging mode selected, the fluorescence camera head 44 produces electronic signals that are routed to a dual channel fluorescence camera control unit within the control center 20 (not shown) that converts the electronic signals to standard video signals. The video signals are then routed through the video I/O 32 to the imaging board 28 where they are processed before being displayed on the RGB video monitor 54.
- the position of the mode switch mechanism 67 is selected to project the reflected illumination light onto an RGB video camera head 46.
- the electronic signals produced by the camera head 46 are supplied to an RGB camera control unit 48 that is external to the control center 20, where they are converted to RGB video signals.
- the white light RGB video signals are also routed through the video I/O 32 to the imaging board 28 and are processed before being displayed on the RGB video monitor 54.
- the RGB video camera control unit 48 includes an automatic gain control circuit that also has the capability of adjusting the intensity of the light produced by the combination light source 36 when the system is operating in white light mode.
- the automatic gain control signals for the white light mode are transmitted to the combination light source on a lead 110. -8-
- a keyboard 52 interfaces with the control center 20 through the digital I/O 32 on the computer motherboard and allows the operator to enter patient data or to change the operating parameters of the imaging system.
- the RGB video monitor 54 is connected to the control center 20 through the video I/O 32.
- a VCR 56 may be connected so that video images can be recorded for later review and analysis.
- a video printer 58 allows a physician to print hard copies of a video frame. Images may also be recorded by a film recorder 60 or stored on a magneto-optical disk 62. To allow a user to control the operation of the imaging system, several programmable operator input devices are provided.
- a footswitch 64 and three operator control switches 65 on the camera head 42 allow the operator to remotely activate various control center 20 functions such as freezing and storing images, selecting different AGC modes, or to control some of the peripheral devices such as the video printer 58, film recorder 60, or magneto optical disk 62.
- FIGURE 2 illustrates in further detail the combination light source 36 that is shown in FIGURE 1.
- the light source includes a metal halide lamp 80 that produces broadband white light with mercury (Hg) peaks.
- Light produced by the lamp 80 is passed through a number of filters 82.
- the light is transmitted through either a broadband white light filter (i.e. triple notch filter to remove the Hg peaks) that eliminates the Hg peaks and shapes the spectrum of the metal halide lamp so that it is similar to that of a Xenon lamp.
- a broadband white light filter i.e. triple notch filter to remove the Hg peaks
- light from the lamp is passed through a blue fluorescence excitation light filter that comprises a blue pass band having a center frequency near the mercury peak that occurs at 437 nanometers.
- Light passing through the filters 82 also passes through an adjustable intensity control mechanism 84, which controls the intensity of the light delivered to an endoscope.
- the intensity control 84 is preferably a metal plate with an appropriate shape to block a variable amount of light when it is moved in and out of the light path.
- the light After passing through the intensity control mechanism 84, the light passes through a shutter mechanism 86 that opens to allow the light to enter the illumination guide of the endoscope, if the latter is plugged in.
- the operation of the combination light source 36 is controlled by a microprocessor-based light source controller 90.
- the light source controller 90 controls the operation of a metal halide lamp ballast 92 that provides the operating -9-
- the light source controller provides control signals to a filter driver 94, that physically moves one of the filters 82 into the light path in accordance with time imaging mode selected.
- An intensity control driver 96 receives control signals from the light source controller 90 in order to move the intensity control 84 in and out of the light path, and thereby varies the intensity of the light that reaches the illumination guide of the endoscope.
- the light source controller 90 also sends control signals to a shutter driver/motor 98 that causes the shutter mechanism 86 to open and close.
- the light source controller 90 In addition to controlling the components that adjust the intensity and wavelength of light that is provided to the illumination guide of the endoscope, the light source controller 90 also interfaces with a number of front panel switches 100 that allow a physician to manually adjust the operation of the light source. Alternatively, the light source controller 90 receives commands to control the light source from an interface to the status and control lines 102 that is coupled to the control center 20 that controls the overall operation of the imaging system as shown in FIGURE 1.
- the light source controller 90 To change the output of the combination light source 36 from white illumination light to blue excitation light or vice versa, as well as to control the intensity of the light produced, the light source controller 90 also receives control signals from the control center on lead 106 that indicate which of the filters 82 should be placed into the light path in order to create the white light illumination or blue excitation light.
- the light source controller 90 receives signals from the control center on the status and control lines 108 that indicate whether the intensity of the excitation light produced should be increased or decreased.
- the light source controller 90 receives signals from the RGB video camera control unit 48 on the lead 110 that adjusts the intensity of the white illumination light produced.
- the imaging system of the present invention includes a fluorescence mode automatic gain control (AGC) circuit 30 as shown in FIGURE 3.
- AGC fluorescence mode automatic gain control
- the imaging system can also be operated under manual control as the current Xillix LIFE-Lung Fluorescence Endoscopy SystemTM.
- the implementation of the fluorescence mode AGC is as follows: As described previously, autofluorescence light produced by the tissue under examination is divided into a pair of spectral bands and projected onto a pair of high sensitivity imaging devices such as a pair of electron bombarded CCD's or image intensified CCD transducers 44a and 44b.
- transducer 44a receives the light in a wavelength band ⁇ i, which is located in the green portion of the visible spectrum, while the transducer 44b receives light in a wavelength band ⁇ 2 , which is located in the red portion of the visible spectrum.
- the electronic signals produced by the intensified CCD transducers 44a and 44b are supplied to camera control units (CCUs) 45a and 45b within the control center 20, where they are converted into video signals and routed through the video I/O 32 to the imaging board 28 and to the AGC circuit.
- CCUs camera control units
- the video signals routed to the AGC circuit are applied to a time-over- threshold counter circuit 112.
- the counter circuit also receives a clock signal which is gated by the horizontal and vertical sync signals from the CCUs.
- the counter 112 produces a number of outputs #T1, #T2, . . .#Tn, each of which contains a value which is proportional to the area in one or more video fields that has an intensity level above an associated predefined threshold intensity value.
- Each of the output values #T1, . . .#Tn may be weighted by a function ai, . . .a n 114 before being supplied to a decision tree algorithm 116.
- the decision tree algorithm 116 determines if the gain of the imaging system and/or the intensity of the light produced by the combination light source 36 should be increased or decreased.
- the output of the decision tree algorithm 116 indicates the amount by which the gain should be increased/decreased and this signal is supplied to a gain control equation 120.
- the gain control calculates the amount by which the light source intensity and/or the gain of the individual intensified CCD transducers 44a and 44b of the imaging system should be adjusted to meet the gain change determined by the decision tree algorithm, while maintaining a predefined gain relationship between the two channels.
- the gain control equation 120 produces a pair of binary numbers whose magnitude will result in a proportional gain change in the two ICCDs.
- An increase/decrease gain control circuit 122 receives the binary numbers from the gain control equation 120 and converts the binary numbers received into a pair of voltage levels that are supplied to a pair of transducer gain controls 124 and 126.
- the transducer gain controls 124 and 126 adjust the absolute gain of the intensified CCD transducers 44a and 44b respectively.
- FIGURE 4 illustrates in greater detail the time-over-threshold counter 112 described above.
- the counter 112 operates to produce numeric counts that are indicative of how long a threshold intensity is exceeded in one or more video frames. These numeric counts are proportional to the area in an image with an intensity above -11-
- a bank of independently programmable, reference threshold digital-to-analog converters 140 is programmed by the control center 20 to set a series of reference threshold levels against which the video signals from the CCUs are compared.
- the particular reference threshold levels are selected to represent a percentage of the zero to full scale video signal that is produced by the CCUs and their chosen values are generally dependent on the type of tissue being examined, as will be described below.
- the reference thresholds are applied to the inverting inputs of a number of comparators 144. For example, a voltage equal to 45% of the full scale range of the green channel video signal is supplied on a lead 142a to an inverting input of a comparator 144a. Similarly, a voltage equal to 75% of the full scale range is supplied on a lead 142b to an inverting input of a comparator 144b, Another set of reference threshold voltages are applied to a set of comparators that receive the video signal produced by the red channel CCU. In the presently preferred embodiment of the invention, one reference threshold for each channel is set at a desired peak value while the other reference threshold is set at a desired average intensity value.
- the video signals produced by the dual channel fluorescence CCUs are applied to the noninverting inputs of the comparator circuits 144.
- the comparators 144 produce logic high signals.
- Associated with each of the comparators 144 is a 24-bit counter 146.
- Each counter has a counter enable pin coupled to the output of its associated comparator such that when the comparator produces the logic high signal, the counter is enabled.
- the automatic gain control circuit 30 includes a free nning clock 150 having a frequency that is substantially equal to the pixel clock of the CCUs.
- a sync delay and gating circuit 152 receives the horizontal and vertical synchronization signals produced by the CCUs and only passes the free running clock 150, during the active portions of the video signals.
- the sync delay and gating circuit 152 also produces a field clock pulse for each field of the video signals received. The pulses are counted by a short counter 154 in order to keep track of the number of field periods associated with the values contained in the time-over- threshold counters.
- the counters 146 When the counters 146 are enabled by their corresponding comparator circuits 144, the counters 146 count the number of sync-gated clock pulses that occur during the time when the video signals produced by the red or green channel CCUs -12-
- the values in the counters 146 are read out through a counter readout control circuit 160 that connects the counters 146 to the imaging system's data bus 130 located on a motherboard within the control center 20.
- the counter readout control circuit also receives the count held in the short counter 154.
- the short counter 154 allows the software to be programmed to read out the counters 146 at periodic intervals, such as every ten fields, etc.
- the presently preferred embodiment of the invention utilizes two reference thresholds for each of the green and red channels, additional threshold counters can be added to the automatic gain control circuit in the manner described above if it is desired to obtain more detailed information on the distribution of the video signal amplitudes.
- FIGURE 5 illustrates the steps performed by the decision tree algorithm 116 and the gain control equation 120 shown in FIGURE 3 to adjust the gain of the ICCDs and the light source intensity.
- FIGURE 5 illustrates the two basic processes used to implement the automatic gain control, namely, i) the setup of the parameters in steps 162 and 164, and ii) the running of the decision tree algorithm and gain control equation in steps 166 to 172. Beginning with a step 162, the peak and average reference thresholds are set.
- the thresholds are selected to ensure that all details remain visible. For example, when viewing a body cavity containing detailed structure such as the bronchi, the peak reference threshold may be set at 90% of the full scale value and the average reference threshold set at 50% of the full scale value. Alternatively, if the body cavity being examined is relatively homogeneous, such as the stomach, the reference threshold values may be set such that the average intensity of the image ensures a relatively bright image. For example, the peak reference threshold may be set at 80% of full scale and the average reference threshold set at 60% of full scale. Preprogrammed thresholds selected for commonly viewed tissue samples can be selected or custom values can be entered.
- the automatic gain control circuit selects a number of AGC image fill goal values. These values represent the nominal image area for which the video signal amplitude must be greater than or equal to a particular threshold. For -13-
- fill goal values may be chosen such that 2% of the image area has video signal amplitudes greater than the peak threshold value and 55% of the image area has video signal amplitudes greater than the average threshold value.
- the automatic gain control circuit adjusts the gain of the ICCDs and/or the intensity of the light source such that the image intensity distribution calculated from the time-over-threshold counter 112 achieves the best match to the desired image fill goal values.
- the fill goal values are selected by the operator of the system.
- Step 166 is the first step in the actual AGC decision tree algorithm.
- the automatic gain control circuit waits for the last gain change to take effect and then measures the image intensity distribution for specified number fields.
- the values from the counters 146 in the time-over-threshold counter circuit 112 are read and the image areas analyzed.
- the image area having video signal amplitudes above the higher, or "peak” threshold, and the image area having video signal amplitudes above the lower, or “average” threshold, are applied to the decision tree at step 168.
- the decision tree determines whether the gain should be changed so that the intensity distribution will better meet the AGC fill goal values desired.
- the image area allowed to exceed the peak or the average threshold may be weighted by the functions 114, in order to make the automatic gain control circuit operate more like a peak or average value control circuit as desired for the particular viewing situation.
- the amount of gain change determined by the decision tree algorithm 116 is modified by well known process control techniques at a step 170 to optimize transient behavior such as overshoot, settling time, and oscillatory behavior.
- process control techniques include a leaky integrator function, deadband control, control function mapping, proportional control, and rate and range limiting actions on the next applied gain change. These techniques ensure gain changes occur as quickly as possible without creating stability problems.
- the gain change for the green or red channel ICCD is determined and if required, the amount of light source intensity change.
- the gain change is modified by the control techniques and is applied to the gain control equation 120.
- This equation relates the gain setting of the ICCD in each of the two channels, such that the ratio (first order polynomial) of the gains between the two channels is maintained.
- the ratio of the gains between the two channels may be selected by the system operator. The operator may adjust the ratio, such that the resulting video image appears more red or more green as desired. In the presently -14-
- the relative gain of the ICCD in the red channel to the ICCD in the green channel can be varied over a range of 0.75 to 3.
- the situation may occur that the required fluorescence camera gain falls outside of the optimal gain adjustment range of the ICCD in one or both of the channels. If the calculated gain setting of either channel is greater than the maximum optimal setting or smaller than the minimum optimal setting, then the intensity of the excitation light source is increased or decreased by a fixed amount. The intensity of the light produced by the light source is adjusted a sufficient amount to return the camera gain settings to within the optimal working range.
- a pseudocode listing of the decision tree algorithm 116 and gain control equation 120 is set forth in Appendix A.
- the present invention also includes a two part mode switch mechanism (one part in the light source and one part in the combination camera head) that allows for convenient switching between white light and fluorescence endoscopy imaging modes.
- FIGURE 6 is a schematic block diagram of the mode switching mechanism of the combination camera head.
- the switching mode mechanism of the light source is shown in FIGURE 2.
- the preferred embodiment of the mechanism requires the endoscope to be attached to the combination light source 36 and the combination camera head 42 by means of the endoscope connector 180.
- the combination light source 36 is capable of providing white light (reflectance) illumination and blue light (fluorescence excitation) illumination.
- the combination camera head 42 is capable of transducing three channel RGB reflectance images and two channel fluorescence images.
- the mode switching mechanism is composed of two parts.
- the two parts of the mechanism are linked through control signals via the imaging system control center 20 and the light source system controller 90.
- a light source part of the mode switch consists of the filter driver 94 and the white light an blue light filters 82.
- the filter driver 94 responds to instructions from the light source system controller 90 and positions the appropriate filter in the light path between the lamp and the endoscope illumination guide. The status of the filter driver 94 is also monitored by the light source system controller 90, which then -15-
- control center 20 communicates with the control center 20 via the interface to the status and control lines 102.
- a second part of the mode switching mechanism is located in the combination camera head 42.
- This part of the mode switching mechanism 67 utilizes a movable light path directing mechanism such as a mirror 186.
- a movable light path directing mechanism such as a mirror 186.
- the mirror When in the imaging system is in fluorescence imaging mode, the mirror is moved out of the light path between the endoscope eyepiece and the fluorescence camera head 44. In this way the fluorescence light reaches the dichroic mirror 182 that separates spectrally ⁇ i and ⁇ 2 into their respective optical paths.
- the mirror 186 is moved into the light path. In this position, light from the endoscope is directed to a second, fixed mirror 190, where the light path is folded to form a periscope that redirects the light from the endoscope eyepiece to the RGB video camera head 46.
- both parts of the mode switching mechanism is controlled by an operator input on the combination camera head 42.
- the operator initiates a switch 65 to change the operation of the imaging system. This results in a signal being sent to the control center indicating that a switch of imaging modes has been initiated.
- a signal is generated by a pair of electrical or optical proximity switches 192, 194 in the combination camera head 42 that sense the position of the movable mirror 186.
- a second signal is generated by switches 192, 194 and sent to the control center 20 when the movable mirror 186 has reached its new position.
- the switches 192, 194 function as a safety mechanism for the ICCDs in the fluorescence camera head.
- the ICCDs are susceptible to damage from bright light (e.g. white light reflectance images from the endoscope eyepiece). If the movable mirror 186 is not completely in the fluorescence mode imaging position, the control center 20 reacts by immediately shutting off the power to the ICCDs, thereby protecting them from exposure to possibly damaging iUumination.
- the control center 20 reacts differently to the switch signals depending on whether the operator is switching from fluorescence imaging mode into the white light imaging mode or from white light imaging mode into the fluorescence imaging mode. In the former case, the control center 20 reacts to the first switch signal by immediately shutting off the power to the ICCDs and stopping the display of all images.
- the control center 20 receives the second switch signal, indicating that the movable mirror 186 in the camera head 42 has reached the white light imaging mode position, the control center sends a signal to the light source system -16-
- the light source system controller 90 instructing it to move the white light filter into the light path.
- the light source system controller 90 When the light source mode switch has completed the filter change, the light source system controller 90 generates a light source status signal, which is transmitted to the control center 20.
- the control signal Upon receipt of the light source status signal, the control signal routes the video signal from the RGB video camera control unit 48 to the RGB video monitor 54 and the resulting white light image is displayed.
- the control center 20 reacts to the first switch signal from the combination camera head 42 by sending a signal to the light source system controller 90 instructing it to move the blue light filter into the light path.
- a light source status signal is generated and sent the control center 20 when the light source mode switch has completed the filter change.
- the control center also receives the second switch signal from the combination camera head 42, indicating that the movable mirror 186 has reached the fluorescence imaging mode position, the control center energizes the ICCDs in the fluorescence camera head 44 and routes the video signals from the fluorescence camera control units to the RGB video monitor 54. The resulting fluorescence image is displayed on the RGB video monitor 54. If the incorrect light source status signal is received by the control center 20, the ICCDs in the fluorescence camera head will not be energized, even if the second switch signal has been received from the combination camera head 42.
- the imaging system of the present invention quantifies the relative brightness of the autofluorescence light produced by the tissue in each of the spectral bands ⁇ j and ⁇ 2 in an objective manner.
- FIGURE 7 shows a monitor display 200 with an image 202 of the tissue under examination. Differences in the autofluorescence spectrum produced by normal and abnormal tissue are shown as areas of different color in the image. For example, abnormal tissue 204 produces proportionally less autofluorescence light in the green portion of the spectrum than normal tissue and is shown as a reddish area in the displayed image.
- the relative brightness of the autofluorescence light in the green and red wavebands imaged by the system, ⁇ i and ⁇ 2 can be used as a measure of the difference in the actual fluorescence emission spectra of normal and abnormal tissue.
- a ratio (or other function relating the ⁇ i to the ⁇ 2 waveband) of the brightness of the tissue autofluorescence in the green and red spectral bands is calculated and displayed to the physician. The ratio is calculated for a small area such as a -17-
- the color ratio displayed represents the average color ratio of the tissue imaged within the bounds of area 206.
- the area 206 is shown as a particular area located in the center of the field of view, other locations within the field of view and larger or smaller areas could be used.
- the ratio calculation is implemented as follows: As described above, the video signals from the fluorescence camera control units are routed to the imaging board 28.
- the imaging board 28 digitizes the video signals such that the video signal amplitudes correspond proportionally to digital grey level values.
- the central processing unit 22 within the control center 20 reads the data digitized by the imaging board 28 and sums the grey level values of all the red channel digital data within area 206 and divides that sum by the sum of all the green channel data within area 206. The quotient of these two sums is shown as a dimensionless number 208 on the monitor.
- other non- visual cues could be used to quantify the relative brightness of the tissue autofluorescence in spectral wavebands ⁇ i and ⁇ 2 . For example, a tone having a frequency that is dependent upon the ratio of the brightness of the autofluorescence in each spectral band could be produced. Similarly, the frequency of a blinking light could be made to change in proportion to the changing ratio.
- HVPSON REM ANY WRITE TO ODD ADDRESS IN RANGE OF &H60 TO &H7F SETS TO ON POKE &H61, 0: REM ENERGIZE ICCD HVPS RETURN -39-
- HVPSOFF REM ANY WRITE TO EVEN ADDRESS IN RANGE OF &H60 TO &H7F SETS TO OFF POKE &H60, 0: REM DE-ENERGIZE ICCD HVPS RETURN
Abstract
Description
Claims
Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AT99916553T ATE299354T1 (en) | 1998-04-20 | 1999-04-09 | IMAGING SYSTEM WITH AUTOMATIC GAIN CONTROL FOR REFLECTION AND FLUORESCENCE DOSCOPY |
EP99916553A EP1073365B1 (en) | 1998-04-20 | 1999-04-09 | Imaging system with automatic gain control for reflectance and fluorescence endoscopy |
AU34850/99A AU3485099A (en) | 1998-04-20 | 1999-04-09 | Imaging system with automatic gain control for reflectance and fluorescence endoscopy |
DE69926120T DE69926120T2 (en) | 1998-04-20 | 1999-04-09 | PICTURE SYSTEM WITH AUTOMATIC GAIN CONTROL FOR REFLECTION AND FLUORESCENCE DOCOPY |
JP2000544247A JP2002512067A (en) | 1998-04-20 | 1999-04-09 | Imaging system with automatic gain control for reflection and fluorescence endoscopy |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/064,667 | 1998-04-20 | ||
US09/064,667 US6462770B1 (en) | 1998-04-20 | 1998-04-20 | Imaging system with automatic gain control for reflectance and fluorescence endoscopy |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1999053832A1 true WO1999053832A1 (en) | 1999-10-28 |
Family
ID=22057495
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1999/007789 WO1999053832A1 (en) | 1998-04-20 | 1999-04-09 | Imaging system with automatic gain control for reflectance and fluorescence endoscopy |
Country Status (7)
Country | Link |
---|---|
US (2) | US6462770B1 (en) |
EP (1) | EP1073365B1 (en) |
JP (1) | JP2002512067A (en) |
AT (1) | ATE299354T1 (en) |
AU (1) | AU3485099A (en) |
DE (1) | DE69926120T2 (en) |
WO (1) | WO1999053832A1 (en) |
Cited By (35)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2001095795A2 (en) * | 2000-06-15 | 2001-12-20 | Spectros Corporation | Optical imaging of induced signals in vivo under ambient light conditions |
EP1167951A1 (en) * | 2000-06-26 | 2002-01-02 | Fuji Photo Film Co., Ltd. | Fluorescent image obtaining apparatus |
EP1177761A2 (en) * | 2000-08-02 | 2002-02-06 | Fuji Photo Film Co., Ltd. | Fluorescent-light image display method and apparatus therefor |
US6364829B1 (en) | 1999-01-26 | 2002-04-02 | Newton Laboratories, Inc. | Autofluorescence imaging system for endoscopy |
WO2002007587A3 (en) * | 2000-07-14 | 2002-04-25 | Xillix Technologies Corp | Compact fluorescent endoscopy video system |
EP1210907A1 (en) * | 2000-12-04 | 2002-06-05 | Fuji Photo Film Co., Ltd. | Fluorescent image obtaining apparatus |
WO2002050518A2 (en) * | 2000-12-19 | 2002-06-27 | Haishan Zeng | Methods and apparatus for contemporaneous fluoresence and reflectance measurements with multiple measuring devices |
DE10124340A1 (en) * | 2001-05-18 | 2002-12-05 | Fraunhofer Ges Forschung | Method of analyzing a biological sample |
JP2004105533A (en) * | 2002-09-19 | 2004-04-08 | Olympus Corp | Endoscopic surgical system |
EP1637062A1 (en) * | 2003-06-19 | 2006-03-22 | Olympus Corporation | Endoscopic device |
WO2008070269A2 (en) * | 2006-10-06 | 2008-06-12 | Novadaq Technologies, Inc. | Methods, software and systems for imaging |
US7846091B2 (en) | 1999-01-26 | 2010-12-07 | Newton Laboratories, Inc. | Autofluorescence imaging system for endoscopy |
CN103118582A (en) * | 2010-09-22 | 2013-05-22 | 奥林巴斯株式会社 | Fluorescence observation device |
US8630698B2 (en) | 2005-05-04 | 2014-01-14 | Novadaq Technologies, Inc. | Filter for use with imaging endoscopes |
US9386909B2 (en) | 2006-07-28 | 2016-07-12 | Novadaq Technologies Inc. | System and method for deposition and removal of an optical element on an endoscope objective |
US9610021B2 (en) | 2008-01-25 | 2017-04-04 | Novadaq Technologies Inc. | Method for evaluating blush in myocardial tissue |
US9642532B2 (en) | 2008-03-18 | 2017-05-09 | Novadaq Technologies Inc. | Imaging system for combined full-color reflectance and near-infrared imaging |
US9816930B2 (en) | 2014-09-29 | 2017-11-14 | Novadaq Technologies Inc. | Imaging a target fluorophore in a biological material in the presence of autofluorescence |
US9814378B2 (en) | 2011-03-08 | 2017-11-14 | Novadaq Technologies Inc. | Full spectrum LED illuminator having a mechanical enclosure and heatsink |
US9877654B2 (en) | 2006-02-07 | 2018-01-30 | Novadaq Technologies Inc. | Near infrared imaging |
US10041042B2 (en) | 2008-05-02 | 2018-08-07 | Novadaq Technologies ULC | Methods for production and use of substance-loaded erythrocytes (S-IEs) for observation and treatment of microvascular hemodynamics |
US10219742B2 (en) | 2008-04-14 | 2019-03-05 | Novadaq Technologies ULC | Locating and analyzing perforator flaps for plastic and reconstructive surgery |
US10265419B2 (en) | 2005-09-02 | 2019-04-23 | Novadaq Technologies ULC | Intraoperative determination of nerve location |
US10278585B2 (en) | 2012-06-21 | 2019-05-07 | Novadaq Technologies ULC | Quantification and analysis of angiography and perfusion |
US10293122B2 (en) | 2016-03-17 | 2019-05-21 | Novadaq Technologies ULC | Endoluminal introducer with contamination avoidance |
DE102017222530A1 (en) * | 2017-12-12 | 2019-06-13 | Henkel Ag & Co. Kgaa | Arrangement for determining metabolic end products in the skin |
US10434190B2 (en) | 2006-09-07 | 2019-10-08 | Novadaq Technologies ULC | Pre-and-intra-operative localization of penile sentinel nodes |
US10492671B2 (en) | 2009-05-08 | 2019-12-03 | Novadaq Technologies ULC | Near infra red fluorescence imaging for visualization of blood vessels during endoscopic harvest |
US10631746B2 (en) | 2014-10-09 | 2020-04-28 | Novadaq Technologies ULC | Quantification of absolute blood flow in tissue using fluorescence-mediated photoplethysmography |
US10694151B2 (en) | 2006-12-22 | 2020-06-23 | Novadaq Technologies ULC | Imaging system with a single color image sensor for simultaneous fluorescence and color video endoscopy |
US10869645B2 (en) | 2016-06-14 | 2020-12-22 | Stryker European Operations Limited | Methods and systems for adaptive imaging for low light signal enhancement in medical visualization |
USD916294S1 (en) | 2016-04-28 | 2021-04-13 | Stryker European Operations Limited | Illumination and imaging device |
US10980420B2 (en) | 2016-01-26 | 2021-04-20 | Stryker European Operations Limited | Configurable platform |
US10992848B2 (en) | 2017-02-10 | 2021-04-27 | Novadaq Technologies ULC | Open-field handheld fluorescence imaging systems and methods |
US11930278B2 (en) | 2015-11-13 | 2024-03-12 | Stryker Corporation | Systems and methods for illumination and imaging of a target |
Families Citing this family (146)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6462770B1 (en) * | 1998-04-20 | 2002-10-08 | Xillix Technologies Corp. | Imaging system with automatic gain control for reflectance and fluorescence endoscopy |
US7136098B1 (en) * | 1998-10-23 | 2006-11-14 | Smith & Nephew, Inc. | Image illumination optimizing |
US6902527B1 (en) * | 1999-05-18 | 2005-06-07 | Olympus Corporation | Endoscope system with charge multiplying imaging device and automatic gain control |
US7134557B2 (en) * | 2000-02-04 | 2006-11-14 | Bratten Jack R | Lift station and method |
JP2002045329A (en) * | 2000-08-01 | 2002-02-12 | Fuji Photo Film Co Ltd | Fluorescent device displaying diagnostic image |
US7321394B1 (en) * | 2000-09-29 | 2008-01-22 | Lucid, Inc. | Automatic gain control for a confocal imaging system |
US6697652B2 (en) | 2001-01-19 | 2004-02-24 | Massachusetts Institute Of Technology | Fluorescence, reflectance and light scattering spectroscopy for measuring tissue |
DE10116859C2 (en) * | 2001-04-04 | 2003-10-09 | Wolf Gmbh Richard | Tissue diagnostic imaging device |
JP2002345733A (en) * | 2001-05-29 | 2002-12-03 | Fuji Photo Film Co Ltd | Imaging device |
IL155046A (en) * | 2003-03-23 | 2013-12-31 | Given Imaging Ltd | In-vivo imaging device capable of defining its location |
US9149175B2 (en) * | 2001-07-26 | 2015-10-06 | Given Imaging Ltd. | Apparatus and method for light control in an in-vivo imaging device |
US20060184039A1 (en) * | 2001-07-26 | 2006-08-17 | Dov Avni | Apparatus and method for light control in an in-vivo imaging device |
JP4772235B2 (en) * | 2001-09-13 | 2011-09-14 | オリンパス株式会社 | Endoscope device |
US7404929B2 (en) * | 2002-01-18 | 2008-07-29 | Newton Laboratories, Inc. | Spectroscopic diagnostic methods and system based on scattering of polarized light |
US7333189B2 (en) * | 2002-01-18 | 2008-02-19 | Pentax Corporation | Spectroscopic diagnostic methods and system |
US20030160865A1 (en) * | 2002-02-27 | 2003-08-28 | Pentax Corporation | Electronic endoscope apparatus including video-processor |
JP2003334162A (en) * | 2002-03-14 | 2003-11-25 | Olympus Optical Co Ltd | Endoscopic image processor |
US6711426B2 (en) * | 2002-04-09 | 2004-03-23 | Spectros Corporation | Spectroscopy illuminator with improved delivery efficiency for high optical density and reduced thermal load |
US8285015B2 (en) * | 2002-07-05 | 2012-10-09 | Lawrence Livermore Natioonal Security, LLC | Simultaneous acquisition of differing image types |
US7164533B2 (en) | 2003-01-22 | 2007-01-16 | Cyvera Corporation | Hybrid random bead/chip based microarray |
US7901630B2 (en) | 2002-08-20 | 2011-03-08 | Illumina, Inc. | Diffraction grating-based encoded microparticle assay stick |
US7923260B2 (en) | 2002-08-20 | 2011-04-12 | Illumina, Inc. | Method of reading encoded particles |
US7872804B2 (en) | 2002-08-20 | 2011-01-18 | Illumina, Inc. | Encoded particle having a grating with variations in the refractive index |
US7900836B2 (en) | 2002-08-20 | 2011-03-08 | Illumina, Inc. | Optical reader system for substrates having an optically readable code |
US7508608B2 (en) | 2004-11-17 | 2009-03-24 | Illumina, Inc. | Lithographically fabricated holographic optical identification element |
US20100255603A9 (en) | 2002-09-12 | 2010-10-07 | Putnam Martin A | Method and apparatus for aligning microbeads in order to interrogate the same |
US7092160B2 (en) | 2002-09-12 | 2006-08-15 | Illumina, Inc. | Method of manufacturing of diffraction grating-based optical identification element |
DE10252313B9 (en) * | 2002-11-11 | 2006-10-19 | Carl Zeiss | Investigation system for the simultaneous direct visualization of a fluorescent label and a tissue region surrounding the fluorescent label and method of investigation therefor |
JP2006509574A (en) * | 2002-12-16 | 2006-03-23 | ギブン イメージング リミテッド | Apparatus, system, and method for selective actuation of in-vivo sensors |
US20040225222A1 (en) | 2003-05-08 | 2004-11-11 | Haishan Zeng | Real-time contemporaneous multimodal imaging and spectroscopy uses thereof |
JP4388318B2 (en) * | 2003-06-27 | 2009-12-24 | オリンパス株式会社 | Image processing device |
US7433123B2 (en) | 2004-02-19 | 2008-10-07 | Illumina, Inc. | Optical identification element having non-waveguide photosensitive substrate with diffraction grating therein |
KR100583250B1 (en) * | 2004-03-05 | 2006-05-24 | 한국전기연구원 | Fluorecence endoscope having improved image detection module |
US7605852B2 (en) | 2004-05-17 | 2009-10-20 | Micron Technology, Inc. | Real-time exposure control for automatic light control |
WO2006020363A2 (en) | 2004-07-21 | 2006-02-23 | Illumina, Inc. | Method and apparatus for drug product tracking using encoded optical identification elements |
US7855727B2 (en) * | 2004-09-15 | 2010-12-21 | Gyrus Acmi, Inc. | Endoscopy device supporting multiple input devices |
DE602005019791D1 (en) | 2004-11-16 | 2010-04-15 | Illumina Inc | METHOD AND DEVICE FOR READING CODED MICROBALLS |
WO2006055735A2 (en) * | 2004-11-16 | 2006-05-26 | Illumina, Inc | Scanner having spatial light modulator |
JP4555093B2 (en) * | 2005-01-05 | 2010-09-29 | Hoya株式会社 | Electronic endoscope system |
JP4786910B2 (en) * | 2005-02-07 | 2011-10-05 | Hoya株式会社 | Electronic endoscope |
US20070167835A1 (en) * | 2005-07-25 | 2007-07-19 | Massachusetts Institute Of Technology | Tri modal spectroscopic imaging |
JP4761882B2 (en) * | 2005-08-10 | 2011-08-31 | オプティスキャン ピーティーワイ リミテッド | Scanning confocal endoscope system and image display range adjustment method of the system |
JP4761899B2 (en) * | 2005-09-12 | 2011-08-31 | Hoya株式会社 | Electronic endoscope system |
US20070173736A1 (en) * | 2005-10-07 | 2007-07-26 | Femspec Llc | Apparatus and methods for endometrial biopsies |
US7830575B2 (en) | 2006-04-10 | 2010-11-09 | Illumina, Inc. | Optical scanner with improved scan time |
US20080058785A1 (en) | 2006-04-12 | 2008-03-06 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Autofluorescent imaging and target ablation |
JP2008043742A (en) * | 2006-07-20 | 2008-02-28 | Pentax Corp | Electronic endoscope system |
FR2904927B1 (en) * | 2006-08-17 | 2018-05-18 | Mauna Kea Technologies | USE OF A FIBER IN VIVO IN SITU CONFOCAL FLUORESCENCE IMAGING SYSTEM, SYSTEM AND METHOD FOR CONFOCAL FIBER IN VIVO IN SITU FLUORESCENCE IMAGING |
US7680373B2 (en) * | 2006-09-13 | 2010-03-16 | University Of Washington | Temperature adjustment in scanning beam devices |
US9079762B2 (en) * | 2006-09-22 | 2015-07-14 | Ethicon Endo-Surgery, Inc. | Micro-electromechanical device |
DE102006050886B4 (en) * | 2006-10-27 | 2016-12-22 | Siemens Healthcare Gmbh | Medical instrument and device for generating tissue sections |
US7738762B2 (en) * | 2006-12-15 | 2010-06-15 | University Of Washington | Attaching optical fibers to actuator tubes with beads acting as spacers and adhesives |
US8244021B2 (en) * | 2006-12-20 | 2012-08-14 | Ventana Medical Systems, Inc. | Quantitative, multispectral image analysis of tissue specimens stained with quantum dots |
US7713265B2 (en) | 2006-12-22 | 2010-05-11 | Ethicon Endo-Surgery, Inc. | Apparatus and method for medically treating a tattoo |
US8801606B2 (en) * | 2007-01-09 | 2014-08-12 | Ethicon Endo-Surgery, Inc. | Method of in vivo monitoring using an imaging system including scanned beam imaging unit |
US8273015B2 (en) | 2007-01-09 | 2012-09-25 | Ethicon Endo-Surgery, Inc. | Methods for imaging the anatomy with an anatomically secured scanner assembly |
US8305432B2 (en) * | 2007-01-10 | 2012-11-06 | University Of Washington | Scanning beam device calibration |
US7589316B2 (en) * | 2007-01-18 | 2009-09-15 | Ethicon Endo-Surgery, Inc. | Scanning beam imaging with adjustable detector sensitivity or gain |
JP2008200173A (en) * | 2007-02-19 | 2008-09-04 | Hoya Corp | Processor for electronic endoscope |
US8216214B2 (en) * | 2007-03-12 | 2012-07-10 | Ethicon Endo-Surgery, Inc. | Power modulation of a scanning beam for imaging, therapy, and/or diagnosis |
US20080242967A1 (en) * | 2007-03-27 | 2008-10-02 | Ethicon Endo-Surgery, Inc. | Medical imaging and therapy utilizing a scanned beam system operating at multiple wavelengths |
US7583872B2 (en) * | 2007-04-05 | 2009-09-01 | University Of Washington | Compact scanning fiber device |
US8626271B2 (en) * | 2007-04-13 | 2014-01-07 | Ethicon Endo-Surgery, Inc. | System and method using fluorescence to examine within a patient's anatomy |
US7995045B2 (en) * | 2007-04-13 | 2011-08-09 | Ethicon Endo-Surgery, Inc. | Combined SBI and conventional image processor |
US7608842B2 (en) * | 2007-04-26 | 2009-10-27 | University Of Washington | Driving scanning fiber devices with variable frequency drive signals |
US20080275305A1 (en) * | 2007-05-01 | 2008-11-06 | Ethicon Endo-Surgery, Inc. | Medical scanned beam imager and components associated therewith |
US20080281159A1 (en) * | 2007-05-08 | 2008-11-13 | University Of Washington | Coordinating image acquisition among multiple endoscopes |
US20080281207A1 (en) * | 2007-05-08 | 2008-11-13 | University Of Washington | Image acquisition through filtering in multiple endoscope systems |
US8212884B2 (en) * | 2007-05-22 | 2012-07-03 | University Of Washington | Scanning beam device having different image acquisition modes |
US8160678B2 (en) * | 2007-06-18 | 2012-04-17 | Ethicon Endo-Surgery, Inc. | Methods and devices for repairing damaged or diseased tissue using a scanning beam assembly |
US7558455B2 (en) | 2007-06-29 | 2009-07-07 | Ethicon Endo-Surgery, Inc | Receiver aperture broadening for scanned beam imaging |
US7982776B2 (en) | 2007-07-13 | 2011-07-19 | Ethicon Endo-Surgery, Inc. | SBI motion artifact removal apparatus and method |
US8437587B2 (en) * | 2007-07-25 | 2013-05-07 | University Of Washington | Actuating an optical fiber with a piezoelectric actuator and detecting voltages generated by the piezoelectric actuator |
US9125552B2 (en) | 2007-07-31 | 2015-09-08 | Ethicon Endo-Surgery, Inc. | Optical scanning module and means for attaching the module to medical instruments for introducing the module into the anatomy |
US7983739B2 (en) * | 2007-08-27 | 2011-07-19 | Ethicon Endo-Surgery, Inc. | Position tracking and control for a scanning assembly |
US7925333B2 (en) * | 2007-08-28 | 2011-04-12 | Ethicon Endo-Surgery, Inc. | Medical device including scanned beam unit with operational control features |
US20090060381A1 (en) * | 2007-08-31 | 2009-03-05 | Ethicon Endo-Surgery, Inc. | Dynamic range and amplitude control for imaging |
US7522813B1 (en) * | 2007-10-04 | 2009-04-21 | University Of Washington | Reducing distortion in scanning fiber devices |
US7995798B2 (en) * | 2007-10-15 | 2011-08-09 | Given Imaging Ltd. | Device, system and method for estimating the size of an object in a body lumen |
US8411922B2 (en) * | 2007-11-30 | 2013-04-02 | University Of Washington | Reducing noise in images acquired with a scanning beam device |
US20090177042A1 (en) * | 2008-01-09 | 2009-07-09 | University Of Washington | Color image acquisition with scanning laser beam devices |
US9072445B2 (en) * | 2008-01-24 | 2015-07-07 | Lifeguard Surgical Systems Inc. | Common bile duct surgical imaging system |
US20090192390A1 (en) * | 2008-01-24 | 2009-07-30 | Lifeguard Surgical Systems | Common bile duct surgical imaging system |
US8050520B2 (en) | 2008-03-27 | 2011-11-01 | Ethicon Endo-Surgery, Inc. | Method for creating a pixel image from sampled data of a scanned beam imager |
JP2009240354A (en) * | 2008-03-28 | 2009-10-22 | Fujinon Corp | Electronic endoscope apparatus |
US8332014B2 (en) | 2008-04-25 | 2012-12-11 | Ethicon Endo-Surgery, Inc. | Scanned beam device and method using same which measures the reflectance of patient tissue |
US20100249607A1 (en) * | 2008-09-26 | 2010-09-30 | Massachusetts Institute Of Technology | Quantitative spectroscopic imaging |
JP2012509715A (en) * | 2008-11-21 | 2012-04-26 | メイヨ・ファウンデーション・フォー・メディカル・エデュケーション・アンド・リサーチ | Colonoscopy tracking and evaluation system |
CN102271573A (en) * | 2009-01-07 | 2011-12-07 | 基文影像公司 | Device and method for detection of an in-vivo pathology |
JP5346635B2 (en) * | 2009-03-24 | 2013-11-20 | オリンパス株式会社 | Fluorescence observation equipment |
JP5361488B2 (en) * | 2009-03-24 | 2013-12-04 | オリンパス株式会社 | Fluorescence observation equipment |
US8461546B2 (en) | 2009-04-03 | 2013-06-11 | Lawrence Livermore National Security, Llc | Compounds for neutron radiation detectors and systems thereof |
US8872125B2 (en) | 2009-04-03 | 2014-10-28 | Lawrence Livermore National Security, Llc | Solution-grown crystals for neutron radiation detectors, and methods of solution growth |
US9872609B2 (en) | 2009-06-18 | 2018-01-23 | Endochoice Innovation Center Ltd. | Multi-camera endoscope |
US9901244B2 (en) | 2009-06-18 | 2018-02-27 | Endochoice, Inc. | Circuit board assembly of a multiple viewing elements endoscope |
US9642513B2 (en) | 2009-06-18 | 2017-05-09 | Endochoice Inc. | Compact multi-viewing element endoscope system |
US9492063B2 (en) | 2009-06-18 | 2016-11-15 | Endochoice Innovation Center Ltd. | Multi-viewing element endoscope |
WO2010146587A1 (en) | 2009-06-18 | 2010-12-23 | Peer Medical Ltd. | Multi-camera endoscope |
US9402533B2 (en) | 2011-03-07 | 2016-08-02 | Endochoice Innovation Center Ltd. | Endoscope circuit board assembly |
US9101268B2 (en) | 2009-06-18 | 2015-08-11 | Endochoice Innovation Center Ltd. | Multi-camera endoscope |
US8926502B2 (en) | 2011-03-07 | 2015-01-06 | Endochoice, Inc. | Multi camera endoscope having a side service channel |
US11547275B2 (en) | 2009-06-18 | 2023-01-10 | Endochoice, Inc. | Compact multi-viewing element endoscope system |
US11864734B2 (en) | 2009-06-18 | 2024-01-09 | Endochoice, Inc. | Multi-camera endoscope |
US9706903B2 (en) | 2009-06-18 | 2017-07-18 | Endochoice, Inc. | Multiple viewing elements endoscope system with modular imaging units |
WO2012077116A1 (en) | 2010-12-09 | 2012-06-14 | Peermedical Ltd. | Flexible electronic circuit board for a multi-camera endoscope |
US11278190B2 (en) | 2009-06-18 | 2022-03-22 | Endochoice, Inc. | Multi-viewing element endoscope |
US10165929B2 (en) | 2009-06-18 | 2019-01-01 | Endochoice, Inc. | Compact multi-viewing element endoscope system |
US9713417B2 (en) | 2009-06-18 | 2017-07-25 | Endochoice, Inc. | Image capture assembly for use in a multi-viewing elements endoscope |
US9101287B2 (en) | 2011-03-07 | 2015-08-11 | Endochoice Innovation Center Ltd. | Multi camera endoscope assembly having multiple working channels |
EP2515759A4 (en) | 2009-12-23 | 2015-01-21 | Given Imaging Inc | Method of evaluating constipation using an ingestible capsule |
JP2011131002A (en) * | 2009-12-25 | 2011-07-07 | Fujifilm Corp | Fluorescent image capturing apparatus |
US9019345B2 (en) * | 2010-07-02 | 2015-04-28 | Intuitive Surgical Operations, Inc. | Imaging mode blooming suppression |
EP2613687B1 (en) | 2010-09-08 | 2016-11-02 | Covidien LP | Catheter with imaging assembly |
US9560953B2 (en) | 2010-09-20 | 2017-02-07 | Endochoice, Inc. | Operational interface in a multi-viewing element endoscope |
US10080486B2 (en) | 2010-09-20 | 2018-09-25 | Endochoice Innovation Center Ltd. | Multi-camera endoscope having fluid channels |
EP3540495A1 (en) | 2010-10-28 | 2019-09-18 | EndoChoice Innovation Center Ltd. | Optical systems for multi-sensor endoscopes |
US11889986B2 (en) | 2010-12-09 | 2024-02-06 | Endochoice, Inc. | Flexible electronic circuit board for a multi-camera endoscope |
EP3420886B8 (en) | 2010-12-09 | 2020-07-15 | EndoChoice, Inc. | Flexible electronic circuit board multi-camera endoscope |
CN103491854B (en) | 2011-02-07 | 2016-08-24 | 恩多卓斯创新中心有限公司 | Multicomponent cover for many cameras endoscope |
DE102011016138A1 (en) * | 2011-03-30 | 2012-10-04 | Karl Storz Gmbh & Co. Kg | Device for fluorescence diagnosis |
US9309456B2 (en) | 2011-04-15 | 2016-04-12 | Lawrence Livermore National Security, Llc | Plastic scintillator with effective pulse shape discrimination for neutron and gamma detection |
JP2013000452A (en) * | 2011-06-20 | 2013-01-07 | Olympus Corp | Electronic endoscope device |
CA2798729A1 (en) | 2011-12-13 | 2013-06-13 | Peermedical Ltd. | Rotatable connector for an endoscope |
CA2798716A1 (en) | 2011-12-13 | 2013-06-13 | Peermedical Ltd. | Removable tip endoscope |
US9121947B2 (en) | 2012-01-23 | 2015-09-01 | Lawrence Livermore National Security, Llc | Stress reduction for pillar filled structures |
US8580054B2 (en) | 2012-04-04 | 2013-11-12 | Lawrence Livermore National Security, Llc | Melt-castable energetic compounds comprising oxadiazoles and methods of production thereof |
US9650564B2 (en) | 2012-05-14 | 2017-05-16 | Lawrence Livermore National Security, Llc | System and plastic scintillator for discrimination of thermal neutron, fast neutron, and gamma radiation |
US9560954B2 (en) | 2012-07-24 | 2017-02-07 | Endochoice, Inc. | Connector for use with endoscope |
US9198835B2 (en) | 2012-09-07 | 2015-12-01 | Covidien Lp | Catheter with imaging assembly with placement aid and related methods therefor |
USD717340S1 (en) | 2012-09-07 | 2014-11-11 | Covidien Lp | Display screen with enteral feeding icon |
US9517184B2 (en) | 2012-09-07 | 2016-12-13 | Covidien Lp | Feeding tube with insufflation device and related methods therefor |
USD716841S1 (en) | 2012-09-07 | 2014-11-04 | Covidien Lp | Display screen with annotate file icon |
USD735343S1 (en) | 2012-09-07 | 2015-07-28 | Covidien Lp | Console |
US9986899B2 (en) | 2013-03-28 | 2018-06-05 | Endochoice, Inc. | Manifold for a multiple viewing elements endoscope |
US9993142B2 (en) | 2013-03-28 | 2018-06-12 | Endochoice, Inc. | Fluid distribution device for a multiple viewing elements endoscope |
US10499794B2 (en) | 2013-05-09 | 2019-12-10 | Endochoice, Inc. | Operational interface in a multi-viewing element endoscope |
US9274237B2 (en) | 2013-07-26 | 2016-03-01 | Lawrence Livermore National Security, Llc | Lithium-containing scintillators for thermal neutron, fast neutron, and gamma detection |
JP6353288B2 (en) * | 2014-06-19 | 2018-07-04 | オリンパス株式会社 | Optical scanning endoscope device |
CN105934946B (en) * | 2014-08-20 | 2017-06-13 | 奥林巴斯株式会社 | Observation device |
EP3190785A4 (en) * | 2014-09-05 | 2018-03-28 | Olympus Corporation | Imaging device and processing device |
JP6485694B2 (en) * | 2015-03-26 | 2019-03-20 | ソニー株式会社 | Information processing apparatus and method |
AU2018200147B2 (en) * | 2017-01-09 | 2018-11-15 | Verathon Inc. | Upgradable video laryngoscope system exhibiting reduced far end dimming |
WO2019115201A1 (en) * | 2017-12-12 | 2019-06-20 | Koninklijke Philips N.V. | Method and system for automatic brightness/gain control while measuring localized oral inflammation |
WO2019230095A1 (en) * | 2018-05-31 | 2019-12-05 | パナソニックIpマネジメント株式会社 | Camera apparatus, image processing method, and camera system |
EP4213712A1 (en) * | 2020-09-18 | 2023-07-26 | Stryker European Operations Limited | Systems and methods for fluorescence visualization |
CN114081424A (en) * | 2021-10-08 | 2022-02-25 | 深圳迈瑞生物医疗电子股份有限公司 | Endoscopic imaging system and control method thereof |
Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4786813A (en) | 1984-10-22 | 1988-11-22 | Hightech Network Sci Ab | Fluorescence imaging system |
FR2671405A1 (en) * | 1991-01-04 | 1992-07-10 | Inst Nat Sante Rech Med | DEVICE FOR MEASURING THE PH OF A TARGET, METHOD OF USING SAID DEVICE AND ITS APPLICATIONS. |
WO1995026673A2 (en) * | 1994-03-28 | 1995-10-12 | Xillix Technologies Corporation | Apparatus and method for imaging diseased tissue using integrated autofluorescence |
US5507287A (en) | 1991-05-08 | 1996-04-16 | Xillix Technologies Corporation | Endoscopic imaging system for diseased tissue |
EP0774865A2 (en) * | 1995-11-17 | 1997-05-21 | SANYO ELECTRIC Co., Ltd. | Video camera with high speed mode |
US5647368A (en) | 1996-02-28 | 1997-07-15 | Xillix Technologies Corp. | Imaging system for detecting diseased tissue using native fluorsecence in the gastrointestinal and respiratory tract |
Family Cites Families (66)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US1290744A (en) | 1916-04-12 | 1919-01-07 | Electric Boat Co | Periscope. |
US2453336A (en) | 1945-03-31 | 1948-11-09 | Eastman Kodak Co | Periscope lens system |
US2857523A (en) | 1955-06-16 | 1958-10-21 | Corso Leonard | Fluoroscopic device |
DE1797250A1 (en) | 1968-09-04 | 1971-08-05 | Rotter Johann Dr | Optical device with at least one imaging optical element for the reproduction of documents of any size and for the enlarged viewing of small documents |
US3582178A (en) | 1969-06-09 | 1971-06-01 | American Optical Corp | Dual viewing teaching microscope with universal reticle projection unit |
US3749494A (en) | 1970-10-26 | 1973-07-31 | Ranging Inc | Gun sighting and ranging mechanism |
US3790248A (en) | 1971-09-07 | 1974-02-05 | A Kellow | Target sighting systems |
US3931593A (en) | 1974-04-22 | 1976-01-06 | Gte Sylvania Incorporated | Laser beam control device |
US3970373A (en) | 1975-02-06 | 1976-07-20 | The United States Of America As Represented By The Secretary Of The Air Force | Mirror steering system |
US3971068A (en) | 1975-08-22 | 1976-07-20 | The United States Of America As Represented By The Secretary Of The Navy | Image processing system |
FR2326715A1 (en) | 1975-10-01 | 1977-04-29 | France Etat | PANORAMIC SIGHT FOR DAY AND NIGHT SIGHTING |
DE2746076C2 (en) | 1977-10-13 | 1984-07-12 | Fa. Carl Zeiss, 7920 Heidenheim | Panoramic periscope for daytime and thermal imaging |
US4149190A (en) | 1977-10-17 | 1979-04-10 | Xerox Corporation | Automatic gain control for video amplifier |
US4155812A (en) | 1977-11-30 | 1979-05-22 | Pfizer Inc. | Fermentation process for converting L-gulonic acid to 2-keto-L-gulonic acid |
US4200801A (en) | 1979-03-28 | 1980-04-29 | The United States Of America As Represented By The United States Department Of Energy | Portable spotter for fluorescent contaminants on surfaces |
US4378571A (en) | 1981-07-06 | 1983-03-29 | Xerox Corporation | Serial analog video processor for charge coupled device imagers |
DE3133641A1 (en) | 1981-08-26 | 1983-03-10 | Philips Patentverwaltung Gmbh, 2000 Hamburg | IR VISOR |
JPS5940830A (en) | 1982-08-31 | 1984-03-06 | 浜松ホトニクス株式会社 | Apparatus for diagnosis of cancer using laser beam pulse |
JPS60167576A (en) | 1984-01-31 | 1985-08-30 | Canon Inc | Image pickup device |
JPS60213534A (en) | 1984-04-06 | 1985-10-25 | Makoto Okamura | Monitor |
US4651200A (en) | 1985-02-04 | 1987-03-17 | National Biomedical Research Foundation | Split-image, multi-power microscopic image display system and method |
US4930516B1 (en) | 1985-11-13 | 1998-08-04 | Laser Diagnostic Instr Inc | Method for detecting cancerous tissue using visible native luminescence |
FR2611337B1 (en) | 1987-02-20 | 1989-05-26 | Thomson Semiconducteurs | AUTOMATIC VIDEO GAIN CONTROL DEVICE |
US4806005A (en) | 1987-03-31 | 1989-02-21 | Schneider Richard T | Spotting system for binoculars and telescopes |
JPH0642882B2 (en) | 1987-04-20 | 1994-06-08 | 富士写真フイルム株式会社 | Desired image signal range determination method |
US4954897A (en) | 1987-05-22 | 1990-09-04 | Nikon Corporation | Electronic still camera system with automatic gain control of image signal amplifier before image signal recording |
US4930883A (en) | 1987-07-06 | 1990-06-05 | Salzman Ronald H | Photovisual star diagonal |
JP2693978B2 (en) | 1988-02-26 | 1997-12-24 | オリンパス光学工業株式会社 | Electronic endoscope device |
JP2594627B2 (en) * | 1988-02-26 | 1997-03-26 | オリンパス光学工業株式会社 | Electronic endoscope device |
JPH0276722U (en) | 1988-12-01 | 1990-06-12 | ||
EP0449883B1 (en) | 1988-12-21 | 1996-01-31 | Massachusetts Institute Of Technology | A method for laser induced fluorescence of tissue |
JP2542089B2 (en) * | 1989-03-16 | 1996-10-09 | オリンパス光学工業株式会社 | Light source device for endoscope |
JP2516007Y2 (en) | 1989-03-17 | 1996-11-06 | 株式会社トプコン | Surgical microscope |
US5421337A (en) | 1989-04-14 | 1995-06-06 | Massachusetts Institute Of Technology | Spectral diagnosis of diseased tissue |
JPH07105871B2 (en) | 1989-06-30 | 1995-11-13 | キヤノン株式会社 | Image reader |
US5264961A (en) | 1989-10-10 | 1993-11-23 | Unisys Corporation | Techniques for trapping beams of infra-red energy |
DE4015346A1 (en) | 1990-05-12 | 1991-11-14 | Wegmann & Co | FIGHTING VEHICLE, IN PARTICULAR FIGHTING TANK, WITH A HAT ARRANGED IN THE ARMORED HOUSING OF THE VEHICLE |
FR2665544B1 (en) | 1990-07-31 | 1993-07-30 | Thomson Trt Defense | DAY-NIGHT OBSERVATION DEVICE. |
US5041852A (en) | 1990-10-18 | 1991-08-20 | Fjui Photo Film Co., Ltd. | Camera shake correction system |
US5121220A (en) | 1991-02-20 | 1992-06-09 | Jason Empire, Inc. | Ocular turret telescope system |
JP3324780B2 (en) | 1991-05-16 | 2002-09-17 | オリンパス光学工業株式会社 | UV microscope |
US5485203A (en) * | 1991-08-12 | 1996-01-16 | Olympus Optical Co., Ltd. | Color misregistration easing system which corrects on a pixel or block basis only when necessary |
US5377686A (en) | 1991-10-11 | 1995-01-03 | The University Of Connecticut | Apparatus for detecting leakage from vascular tissue |
KR950005050Y1 (en) | 1991-12-05 | 1995-06-21 | 삼성전자 주식회사 | Analog circuit for disital camera |
US5214503A (en) | 1992-01-31 | 1993-05-25 | The United States Of America As Represented By The Secretary Of The Army | Color night vision camera system |
US5408263A (en) * | 1992-06-16 | 1995-04-18 | Olympus Optical Co., Ltd. | Electronic endoscope apparatus |
US5535052A (en) | 1992-07-24 | 1996-07-09 | Carl-Zeiss-Stiftung | Laser microscope |
US5295017A (en) | 1992-08-27 | 1994-03-15 | Bio-Rad Laboratories, Inc. | Sample masking using wavelength-selective material |
US5410363A (en) | 1992-12-08 | 1995-04-25 | Lightwave Communications, Inc. | Automatic gain control device for transmitting video signals between two locations by use of a known reference pulse during vertical blanking period so as to control the gain of the video signals at the second location |
JP3247486B2 (en) | 1993-04-26 | 2002-01-15 | ローム株式会社 | Laser beam printer |
US5424841A (en) | 1993-05-28 | 1995-06-13 | Molecular Dynamics | Apparatus for measuring spatial distribution of fluorescence on a substrate |
US5365057A (en) | 1993-07-02 | 1994-11-15 | Litton Systems, Inc. | Light-weight night vision device |
US5371355A (en) | 1993-07-30 | 1994-12-06 | Litton Systems, Inc. | Night vision device with separable modular image intensifier assembly |
US5749830A (en) * | 1993-12-03 | 1998-05-12 | Olympus Optical Co., Ltd. | Fluorescent endoscope apparatus |
JPH07218862A (en) | 1994-02-04 | 1995-08-18 | Canon Inc | Spatial optical transmission equipment |
US5729382A (en) | 1994-07-08 | 1998-03-17 | Olympus Optical Co., Ltd. | Large exit-pupil stereoscopic microscope |
DE19532897A1 (en) | 1994-09-27 | 1996-03-28 | Zeiss Carl Fa | Camera exposure control by image photometry in photographic microscope |
JP3730672B2 (en) * | 1994-10-20 | 2006-01-05 | オリンパス株式会社 | Electronic endoscope device |
JP3411737B2 (en) | 1995-03-03 | 2003-06-03 | ペンタックス株式会社 | Biological fluorescence diagnostic equipment |
US5838001A (en) | 1996-01-31 | 1998-11-17 | Asahi Kogaku Kogyo Kabushiki Kaisha | Scanning optical device and polygon mirror cover |
US6059720A (en) * | 1997-03-07 | 2000-05-09 | Asahi Kogaku Kogyo Kabushiki Kaisha | Endoscope system with amplification of fluorescent image |
JPH1132986A (en) * | 1997-07-16 | 1999-02-09 | Olympus Optical Co Ltd | Endoscope system |
DE19800312A1 (en) | 1998-01-07 | 1999-07-08 | Wolf Gmbh Richard | Diagnostic device for imaging of fluorescent biological tissue areas |
DE69938493T2 (en) * | 1998-01-26 | 2009-05-20 | Massachusetts Institute Of Technology, Cambridge | ENDOSCOPE FOR DETECTING FLUORESCENCE IMAGES |
US6462770B1 (en) * | 1998-04-20 | 2002-10-08 | Xillix Technologies Corp. | Imaging system with automatic gain control for reflectance and fluorescence endoscopy |
US6826424B1 (en) * | 2000-12-19 | 2004-11-30 | Haishan Zeng | Methods and apparatus for fluorescence and reflectance imaging and spectroscopy and for contemporaneous measurements of electromagnetic radiation with multiple measuring devices |
-
1998
- 1998-04-20 US US09/064,667 patent/US6462770B1/en not_active Expired - Fee Related
-
1999
- 1999-04-09 WO PCT/US1999/007789 patent/WO1999053832A1/en active IP Right Grant
- 1999-04-09 AU AU34850/99A patent/AU3485099A/en not_active Abandoned
- 1999-04-09 AT AT99916553T patent/ATE299354T1/en not_active IP Right Cessation
- 1999-04-09 DE DE69926120T patent/DE69926120T2/en not_active Expired - Lifetime
- 1999-04-09 JP JP2000544247A patent/JP2002512067A/en not_active Withdrawn
- 1999-04-09 EP EP99916553A patent/EP1073365B1/en not_active Expired - Lifetime
-
2002
- 2002-02-06 US US10/068,583 patent/US20020093563A1/en not_active Abandoned
Patent Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4786813A (en) | 1984-10-22 | 1988-11-22 | Hightech Network Sci Ab | Fluorescence imaging system |
FR2671405A1 (en) * | 1991-01-04 | 1992-07-10 | Inst Nat Sante Rech Med | DEVICE FOR MEASURING THE PH OF A TARGET, METHOD OF USING SAID DEVICE AND ITS APPLICATIONS. |
US5507287A (en) | 1991-05-08 | 1996-04-16 | Xillix Technologies Corporation | Endoscopic imaging system for diseased tissue |
WO1995026673A2 (en) * | 1994-03-28 | 1995-10-12 | Xillix Technologies Corporation | Apparatus and method for imaging diseased tissue using integrated autofluorescence |
EP0774865A2 (en) * | 1995-11-17 | 1997-05-21 | SANYO ELECTRIC Co., Ltd. | Video camera with high speed mode |
US5647368A (en) | 1996-02-28 | 1997-07-15 | Xillix Technologies Corp. | Imaging system for detecting diseased tissue using native fluorsecence in the gastrointestinal and respiratory tract |
Cited By (72)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7846091B2 (en) | 1999-01-26 | 2010-12-07 | Newton Laboratories, Inc. | Autofluorescence imaging system for endoscopy |
US6364829B1 (en) | 1999-01-26 | 2002-04-02 | Newton Laboratories, Inc. | Autofluorescence imaging system for endoscopy |
US8764643B2 (en) | 1999-01-26 | 2014-07-01 | Hoya Corporation | Autofluorescence imaging system for endoscopy |
WO2001095795A2 (en) * | 2000-06-15 | 2001-12-20 | Spectros Corporation | Optical imaging of induced signals in vivo under ambient light conditions |
US6748259B1 (en) | 2000-06-15 | 2004-06-08 | Spectros Corporation | Optical imaging of induced signals in vivo under ambient light conditions |
WO2001095795A3 (en) * | 2000-06-15 | 2002-06-20 | Spectros Corp | Optical imaging of induced signals in vivo under ambient light conditions |
US7668587B2 (en) | 2000-06-15 | 2010-02-23 | Spectros Corporation | Optical imaging of induced signals in vivo under ambient light conditions |
EP1167951A1 (en) * | 2000-06-26 | 2002-01-02 | Fuji Photo Film Co., Ltd. | Fluorescent image obtaining apparatus |
US7349725B2 (en) | 2000-06-26 | 2008-03-25 | Fujifilm Corporation | Fluorescent image obtaining apparatus |
WO2002007587A3 (en) * | 2000-07-14 | 2002-04-25 | Xillix Technologies Corp | Compact fluorescent endoscopy video system |
US8961403B2 (en) | 2000-07-14 | 2015-02-24 | Novadaq Technologies Inc. | Compact fluorescence endoscopy video system |
US9968244B2 (en) | 2000-07-14 | 2018-05-15 | Novadaq Technologies ULC | Compact fluorescence endoscopy video system |
US6821245B2 (en) | 2000-07-14 | 2004-11-23 | Xillix Technologies Corporation | Compact fluorescence endoscopy video system |
EP1731087A3 (en) * | 2000-07-14 | 2008-08-06 | Novadaq Technologies Inc. | Compact fluorescent endoscopy video system |
US7341557B2 (en) | 2000-07-14 | 2008-03-11 | Novadaq Technologies Inc. | Compact fluorescence endoscopy video system |
EP1177761A2 (en) * | 2000-08-02 | 2002-02-06 | Fuji Photo Film Co., Ltd. | Fluorescent-light image display method and apparatus therefor |
EP1609409A1 (en) * | 2000-08-02 | 2005-12-28 | Fuji Photo Film Co., Ltd | Fluorescent-light image display method and apparatus therefor |
EP1609407A1 (en) * | 2000-08-02 | 2005-12-28 | Fuji Photo Film Co., Ltd | Fluorescent-light image display method and apparatus therefor |
EP1177761B1 (en) * | 2000-08-02 | 2006-10-18 | Fuji Photo Film Co., Ltd. | Fluorescent-light image display method and apparatus therefor |
US7181265B2 (en) | 2000-12-04 | 2007-02-20 | Fuji Photo Film Co., Ltd. | Fluorescent image obtaining apparatus |
EP1210907A1 (en) * | 2000-12-04 | 2002-06-05 | Fuji Photo Film Co., Ltd. | Fluorescent image obtaining apparatus |
WO2002050518A3 (en) * | 2000-12-19 | 2003-05-01 | Haishan Zeng | Methods and apparatus for contemporaneous fluoresence and reflectance measurements with multiple measuring devices |
US7253894B2 (en) | 2000-12-19 | 2007-08-07 | Perceptronix Medical, Inc. | Image detection apparatus for fluorescence and reflectance imaging and spectroscopy and for contemporaneous measurements of electromagnetic radiation with multiple measuring devices |
WO2002050518A2 (en) * | 2000-12-19 | 2002-06-27 | Haishan Zeng | Methods and apparatus for contemporaneous fluoresence and reflectance measurements with multiple measuring devices |
US6898458B2 (en) | 2000-12-19 | 2005-05-24 | Haishan Zeng | Methods and apparatus for fluorescence and reflectance imaging and spectroscopy and for contemporaneous measurements of electromagnetic radiation with multiple measuring devices |
US6826424B1 (en) | 2000-12-19 | 2004-11-30 | Haishan Zeng | Methods and apparatus for fluorescence and reflectance imaging and spectroscopy and for contemporaneous measurements of electromagnetic radiation with multiple measuring devices |
US7190452B2 (en) | 2000-12-19 | 2007-03-13 | Perceptronix Medical, Inc. | Imaging systems for fluorescence and reflectance imaging and spectroscopy and for contemporaneous measurements of electromagnetic radiation with multiple measuring devices |
US7257243B2 (en) | 2001-05-18 | 2007-08-14 | Fraunhofer-Gesellschaft Zur Foerderung Der Angewandten Forschung E.V. | Method for analyzing a biological sample |
DE10124340A1 (en) * | 2001-05-18 | 2002-12-05 | Fraunhofer Ges Forschung | Method of analyzing a biological sample |
US10182709B2 (en) | 2002-01-15 | 2019-01-22 | Novadaq Technologies ULC | Filter for use with imaging endoscopes |
JP2004105533A (en) * | 2002-09-19 | 2004-04-08 | Olympus Corp | Endoscopic surgical system |
EP1637062A4 (en) * | 2003-06-19 | 2010-10-06 | Olympus Corp | Endoscopic device |
EP1637062A1 (en) * | 2003-06-19 | 2006-03-22 | Olympus Corporation | Endoscopic device |
US8630698B2 (en) | 2005-05-04 | 2014-01-14 | Novadaq Technologies, Inc. | Filter for use with imaging endoscopes |
US10265419B2 (en) | 2005-09-02 | 2019-04-23 | Novadaq Technologies ULC | Intraoperative determination of nerve location |
US9877654B2 (en) | 2006-02-07 | 2018-01-30 | Novadaq Technologies Inc. | Near infrared imaging |
US9386909B2 (en) | 2006-07-28 | 2016-07-12 | Novadaq Technologies Inc. | System and method for deposition and removal of an optical element on an endoscope objective |
US10434190B2 (en) | 2006-09-07 | 2019-10-08 | Novadaq Technologies ULC | Pre-and-intra-operative localization of penile sentinel nodes |
WO2008070269A3 (en) * | 2006-10-06 | 2008-09-18 | Novadaq Technologies Inc | Methods, software and systems for imaging |
WO2008070269A2 (en) * | 2006-10-06 | 2008-06-12 | Novadaq Technologies, Inc. | Methods, software and systems for imaging |
US11025867B2 (en) | 2006-12-22 | 2021-06-01 | Stryker European Operations Limited | Imaging systems and methods for displaying fluorescence and visible images |
US10694152B2 (en) | 2006-12-22 | 2020-06-23 | Novadaq Technologies ULC | Imaging systems and methods for displaying fluorescence and visible images |
US11770503B2 (en) | 2006-12-22 | 2023-09-26 | Stryker European Operations Limited | Imaging systems and methods for displaying fluorescence and visible images |
US10694151B2 (en) | 2006-12-22 | 2020-06-23 | Novadaq Technologies ULC | Imaging system with a single color image sensor for simultaneous fluorescence and color video endoscopy |
US10835138B2 (en) | 2008-01-25 | 2020-11-17 | Stryker European Operations Limited | Method for evaluating blush in myocardial tissue |
US9610021B2 (en) | 2008-01-25 | 2017-04-04 | Novadaq Technologies Inc. | Method for evaluating blush in myocardial tissue |
US9936887B2 (en) | 2008-01-25 | 2018-04-10 | Novadaq Technologies ULC | Method for evaluating blush in myocardial tissue |
US11564583B2 (en) | 2008-01-25 | 2023-01-31 | Stryker European Operations Limited | Method for evaluating blush in myocardial tissue |
US9642532B2 (en) | 2008-03-18 | 2017-05-09 | Novadaq Technologies Inc. | Imaging system for combined full-color reflectance and near-infrared imaging |
US10779734B2 (en) | 2008-03-18 | 2020-09-22 | Stryker European Operations Limited | Imaging system for combine full-color reflectance and near-infrared imaging |
US10219742B2 (en) | 2008-04-14 | 2019-03-05 | Novadaq Technologies ULC | Locating and analyzing perforator flaps for plastic and reconstructive surgery |
US10041042B2 (en) | 2008-05-02 | 2018-08-07 | Novadaq Technologies ULC | Methods for production and use of substance-loaded erythrocytes (S-IEs) for observation and treatment of microvascular hemodynamics |
US10492671B2 (en) | 2009-05-08 | 2019-12-03 | Novadaq Technologies ULC | Near infra red fluorescence imaging for visualization of blood vessels during endoscopic harvest |
CN103118582A (en) * | 2010-09-22 | 2013-05-22 | 奥林巴斯株式会社 | Fluorescence observation device |
EP2604169A1 (en) * | 2010-09-22 | 2013-06-19 | Olympus Corporation | Fluorescence observation device |
EP2604169A4 (en) * | 2010-09-22 | 2013-08-28 | Olympus Corp | Fluorescence observation device |
US9814378B2 (en) | 2011-03-08 | 2017-11-14 | Novadaq Technologies Inc. | Full spectrum LED illuminator having a mechanical enclosure and heatsink |
US11284801B2 (en) | 2012-06-21 | 2022-03-29 | Stryker European Operations Limited | Quantification and analysis of angiography and perfusion |
US10278585B2 (en) | 2012-06-21 | 2019-05-07 | Novadaq Technologies ULC | Quantification and analysis of angiography and perfusion |
US9816930B2 (en) | 2014-09-29 | 2017-11-14 | Novadaq Technologies Inc. | Imaging a target fluorophore in a biological material in the presence of autofluorescence |
US10488340B2 (en) | 2014-09-29 | 2019-11-26 | Novadaq Technologies ULC | Imaging a target fluorophore in a biological material in the presence of autofluorescence |
US10631746B2 (en) | 2014-10-09 | 2020-04-28 | Novadaq Technologies ULC | Quantification of absolute blood flow in tissue using fluorescence-mediated photoplethysmography |
US11930278B2 (en) | 2015-11-13 | 2024-03-12 | Stryker Corporation | Systems and methods for illumination and imaging of a target |
US11298024B2 (en) | 2016-01-26 | 2022-04-12 | Stryker European Operations Limited | Configurable platform |
US10980420B2 (en) | 2016-01-26 | 2021-04-20 | Stryker European Operations Limited | Configurable platform |
US10293122B2 (en) | 2016-03-17 | 2019-05-21 | Novadaq Technologies ULC | Endoluminal introducer with contamination avoidance |
USD916294S1 (en) | 2016-04-28 | 2021-04-13 | Stryker European Operations Limited | Illumination and imaging device |
US11756674B2 (en) | 2016-06-14 | 2023-09-12 | Stryker European Operations Limited | Methods and systems for adaptive imaging for low light signal enhancement in medical visualization |
US10869645B2 (en) | 2016-06-14 | 2020-12-22 | Stryker European Operations Limited | Methods and systems for adaptive imaging for low light signal enhancement in medical visualization |
US10992848B2 (en) | 2017-02-10 | 2021-04-27 | Novadaq Technologies ULC | Open-field handheld fluorescence imaging systems and methods |
US11140305B2 (en) | 2017-02-10 | 2021-10-05 | Stryker European Operations Limited | Open-field handheld fluorescence imaging systems and methods |
DE102017222530A1 (en) * | 2017-12-12 | 2019-06-13 | Henkel Ag & Co. Kgaa | Arrangement for determining metabolic end products in the skin |
Also Published As
Publication number | Publication date |
---|---|
JP2002512067A (en) | 2002-04-23 |
AU3485099A (en) | 1999-11-08 |
EP1073365B1 (en) | 2005-07-13 |
DE69926120T2 (en) | 2006-05-11 |
US20020093563A1 (en) | 2002-07-18 |
DE69926120D1 (en) | 2005-08-18 |
US6462770B1 (en) | 2002-10-08 |
ATE299354T1 (en) | 2005-07-15 |
EP1073365A1 (en) | 2001-02-07 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6462770B1 (en) | Imaging system with automatic gain control for reflectance and fluorescence endoscopy | |
US20190082963A1 (en) | Compact fluorescence endoscopy video system | |
EP1880657B1 (en) | Biological observation apparatus | |
EP1889563B1 (en) | Endoscope and image processing device | |
JP3228627B2 (en) | Endoscope image processing device | |
US5647368A (en) | Imaging system for detecting diseased tissue using native fluorsecence in the gastrointestinal and respiratory tract | |
JP5081720B2 (en) | Fluorescence endoscope apparatus and excitation light unit | |
JP4388318B2 (en) | Image processing device | |
US5986271A (en) | Fluorescence imaging system | |
EP1527729B1 (en) | Image processing apparatus | |
JP4098402B2 (en) | Fluorescent imaging device | |
JP3884265B2 (en) | Endoscope device | |
JP3478504B2 (en) | Image processing device | |
CN109561808B (en) | Analysis device | |
JP2005296200A (en) | Image processor for endoscope | |
JP2003126015A (en) | Endoscope |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AK | Designated states |
Kind code of ref document: A1 Designated state(s): AL AM AT AU AZ BA BB BG BR BY CA CH CN CU CZ DE DK EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MD MG MK MN MW MX NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT UA UG US UZ VN YU ZW |
|
AL | Designated countries for regional patents |
Kind code of ref document: A1 Designated state(s): GH GM KE LS MW SD SL SZ UG ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE BF BJ CF CG CI CM GA GN GW ML MR NE SN TD TG |
|
121 | Ep: the epo has been informed by wipo that ep was designated in this application | ||
DFPE | Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101) | ||
ENP | Entry into the national phase |
Ref country code: JP Ref document number: 2000 544247 Kind code of ref document: A Format of ref document f/p: F |
|
NENP | Non-entry into the national phase |
Ref country code: KR |
|
WWE | Wipo information: entry into national phase |
Ref document number: 1999916553 Country of ref document: EP |
|
WWP | Wipo information: published in national office |
Ref document number: 1999916553 Country of ref document: EP |
|
REG | Reference to national code |
Ref country code: DE Ref legal event code: 8642 |
|
WWG | Wipo information: grant in national office |
Ref document number: 1999916553 Country of ref document: EP |